Patent Application
20090254162
The present invention relates to elongated medical devices and more particularly to novel conductor junctions.
Cardiac stimulation systems commonly include a pulse-generating device, such as a pacemaker or implantable cardioverter/defibrillator that is electrically connected to the heart by at least one electrical lead. An electrical lead delivers electrical pulses from the pulse generator to the heart, stimulating the myocardial tissue via electrodes included on the lead. Furthermore, cardiac signals may be sensed by lead electrodes and conducted, via the lead, back to the device, which also monitors the electrical activity of the heart.
Medical electrical leads are typically constructed to have the lowest possible profile without compromising functional integrity, reliability and durability. Often junctions formed between a conductor and other components included in leads, for example electrodes, can increase the lead's profile, therefore it is desirable to develop low profile junctions.
The following drawings are illustrative of particular embodiments of the invention and therefore do not limit its scope, but are presented to assist in providing a proper understanding of the invention. The drawings are not to scale (unless so stated) and are intended for use in conjunction with the explanations in the following detailed description. The present invention will hereinafter be described in conjunction with the appended drawings, wherein like numerals denote like elements, and:
The following detailed description is exemplary in nature and is not intended to limit the scope, applicability, or configuration of the invention in any way. Rather, the following description provides a practical illustration for implementing exemplary embodiments of the invention.
In each of the above described embodiments the openings through which couplings are made between electrodes and conductor fittings may be sealed with an adhesive, for example silicone medical adhesive or polyurethane adhesive, to prevent fluid ingress; sealing may be performed either before or after the coupling depending upon the embodiment.
It will be appreciated by those skilled in the art that while the invention has been described above in connection with particular embodiments and examples, the invention is not necessarily so limited; numerous other embodiments and uses are intended to be encompassed by the claims attached hereto. For example a host of other types of medical devices including electrical mapping catheters, ablation catheters and neurological stimulation devices may employ embodiments of the present invention.
Additional designs are disclosed for medical leads (e.g. next-generation (NG) VT/VF lead etc.) that employ fluoropolymer compounds. Fluoropolymer compounds are commercially available from W. L. Gore & Associates' Electronic Products Division in Elkton, Md. and Newark, Del. Other equivalent materials and processes produced by suppliers may be used.
The fluoropolymer materials include high strength toughened fluoropolymer (HSTF) and/or “expanded polytetrafluoroethylene (e-PTFE). In one embodiment, these materials are composed chemically of PTFE, but are mechanically modified to produce different physical morphologies, which in turn result in different mechanical and electrical properties. With respect to HSTF, the mechanical modification is done to provide enhanced mechanical properties such as tensile strength, abrasion resistance, and resistance to compressive creep or cold-flow, while maintaining a fully dense morphology and associated electrically insulative properties. Mechanical modification to produce e-PTFE on the other hand, results in a porous, open structure, which is not electrically insulative, but possesses comparable strength and abrasion resistance, and more flexibility and kink-resistance than HSTF. Both processes involve extruding and mechanically modifying the materials to produce thin (approximately 0.0002″) sheet, cutting the sheet into tape, and wrapping multiple layers of this tape around conductors, mandrels, and groups of previously wrapped conductors/mandrels to produce lead body subassemblies. In one embodiment, fluorinated ethylene propylene (FEP), a melt-processable PTFE copolymer, is used as a thermal adhesive to bond the layers together. Processing of HSTF and/or e-PTFE can be altered to produce differences in mechanical/electrical properties, including anisotropy in the mechanical properties.
Coated wire and cable components have been evaluated. Dielectric strength testing of HSTF in saline solution, after pre-soaking in IPA to more effectively wet any leak paths present, has shown coatings as thin as 0.0005″ to withstand up to 5000 volts of direct current (DC). HSTF coatings have been shown to have superior compressive creep resistance compared with extruded ETFE coatings.
Layers of e-PTFE can be bonded directly to HSTF to provide structural support, and has been shown to prevent kinking of a thin-walled open lumen tube such as a coil liner, without significantly increasing bending stiffness. Initial evaluations without e-PTFE indicated that although kinking of a coil liner could be reduced by increasing wall thickness to approximately 0.003″ this resulted in stiffness. A composite or layered coil liner, with HSTF on the inside and e-PTFE on the outside, resulted in lower stiffness, comparable size, and kink-resistance, while maintaining acceptable dielectric strength. Use of HSTF and/or e-PTFE Medtronic VT/VF platforms will enable significant downsizing the lead relative to platforms based on multilumen silicone and extruded ETFE insulations. Testing data has shown this material to have superior mechanical and electrical performance compared with extruded ETFE and PTFE.
1. The present invention significantly decreases lead body diameter, compared to lead bodies produced with conventional materials. For instance, with a lead body comprised of one coil with an ETFE liner, three 1×19 cables with extruded ETFE jacketing, housed in multilumen extruded silicone tubing, and a urethane overlay, the introducer size is currently limited to 7 French (Fr).
2. The present invention also performs better under compressive creep or cold-flow conditions, compared with conventionally produced PTFE and ETFE materials. For chronically implanted lead applications, appropriate insulation materials are needed that can withstand the mechanical loading conditions to the extent that electrical insulative properties are maintained for the duration of the implant. Fluoropolymer materials such as PTFE and/or ETFE produced via conventional means have been shown to have inferior creep or cold-flow properties compared with HSTF (e-PTFE may be better as well, although it's not used as an insulative layer). The superior mechanical/electrical performance of the HSTF allows lead body size to be reduced without compromising chronic reliability.
3. Fluoropolymer materials have excellent biocompatibility and chemical biostability properties.
4. The wrapped approach construction is better in terms of coating concentricity and processing-related loss of insulative properties (i.e. pinholes with thin extruded coatings), and is consistent with our business need to automate lead body assembly processes (i.e. eliminates stringing, lead body subassemblies cut-to-length or on-a-spool).
1. Exemplary medical electrical lead body configurations and attributes include, but are not limited to, the following as disclosed below:
Examples of medical electrical lead body configurations and attributes include, but are not limited to, the following as disclosed below:
2. Basic configurations can include conductors 1001 (cables, microcoils, coibles, coiled cables etc.) which are individually wrapped with HSTF and/or ePTFE 1002 (
a. The open tubes or liners 1301 are produced by wrapping HSTF and/or ePTFE tapes 1302 on a ductile mandrel, such as annealed silver-plated copper wire, and subsequently tensile pulling and uniformly necking down the mandrel for removal from the tube.
b. All these individual elements are then wrapped with HSTF and/or ePTFE tapes to produce a complete assembly, or alternatively, a subassembly which could be combined with other subassemblies to form a complete higher-level assembly.
c. All the individual elements and their outer wraps are thermally treated to sinter or bond the individual layers of HSTF and/or ePTFE together. This sintering or bonding can be accomplished by pre-coating or laminating the surfaces with FEP or other fluoropolymer adhesives, or by treating or modifying the surfaces with any other method which results in sintering or bonding between layers.
d. Bonding or sintering of surfaces other than that between layers can be done selectively, as needed. For instance, bonding between individual coated elements can be inhibited to allow relative movement, thereby reducing stiffness. Reduced stiffness can result in less trauma to the vasculature and cardiac tissue, and less risk of tissue perforation during implant and chronic use. An additional benefit of lowered stiffness is lower stresses in conductor and insulation materials.
e. Use of a thinner HSTF, or ePTFE instead of HSTF, for the outermost layer or “outer wrap” can result in reduced stiffness as well.
f. The degree of tightness with which the conductors/cables 1303 are “served” or helically swept or wrapped around a central coil liner tube can affect stiffness and degree of impingement on the coil liner. Impingement on the coil liner can affect the ease of stringing of coils, the ease of to insertion/withdrawal of a stylet, and the ability or effectiveness associated with torque transfer via rotation of a torque conductor coil. The stiffness of the cable materials and cable construct, the degree of residual stress in the individual filaments of the cable, and the residual torsional stress in the served cable, can also affect the degree of impingment on the coil liner. An understanding of the relative degree of impact associated with these factors is necessary to achieve a successful design and manufacturing process.
g. The tightness of the wrapped coating layers can be varied to affect easy of mechanical stripping, or ease of movement between elements, for instance to reduce bending stiffness and flex fatigue resistance.
h. The orientation of the wrapped HSTF and ePTFE layers can alternate between left and right-hand lay or serve, to produce more uniform torsional stiffness and “feel” of the lead body assembly.
i. Any of the wrapped coatings can also be composed of multiple types of materials, for instance alternating layers of HSTF and ePTFE, to affect mechanical or electrical properties. One embodiment can be a composite coil liner consisting of HSTF as the middle layer and ePTFE as the inner and outer layers. Although the ePTFE offers no insulation properties when wetted-out with a conductive fluid, it is more flexible than HSTF and when bonded to the underlying HSTF it can provide structural support or strain relief and help to minimize kinking of the HSTF when bent in small radii (
j. Any of the wrapped coatings or any of the individual layers of each of the coatings, can be made conductive either in selective areas, for instance to facilitate electrical conduction for connection to a component (electrode, connector ring etc.) (
3. The individual conductor and tubular elements described above can be arranged in any number of ways, such as a central lumen to house a coil surrounded by coated cables or coibles (
4. Any of the elements described above can also be of a non-circular cross-section, for example a kidney-shape or tear-drop-shape to better utilize the available space (
5. The elements on the periphery of the cross-sections can be longitudinally configured either linear or straight, or helically swept, “served”, or coiled around the central element with varying degrees of pitch (
6. The outer wrap can be composed of several separate outer wrap sets, with each set effectively encapsulating each separate cable/conductor, thus providing redundant insulation (
7. To facilitate electrical isolation of conductors, fluid sealing, and/or mechanical bonding, the HSTF and ePTFE surfaces can be treated via wet chemical techniques (i.e. Tetra Etch) or plasma techniques (i.e. Medtronic's plasma silane, atmospheric gas plasma, or equivalent processes). Treated surfaces can be done either selectively or on all surfaces, and can be done in tape form or after wrapping/sintering. With these techniques, standard silicone medical adhesive backfill methods can be used to bond and seal as required to provide electrical isolation, fluid leakage, and/or mechanical bonding.
8. Another method of facilitating electrical isolation, fluid sealing, and/or mechanical bonding for strength, can involve use of fluoropolymer or other adhesives. One example is the use of FEP or PFA in selective regions, which can provide effective bonding and sealing. With these materials, bonding could be accomplished during the normal post-wrapping bonding/sintering process (i.e. at the same time the HSTF insulation layers are bonded together), or as a post-processing approach during final lead body assembly. Examples include, but are not limited to, electrical isolation and fluid sealing around defibrillation connectors, and mechanical bonding and fluid sealing of the coil liner to the distal assembly. These approaches may allow minimization or elimination of backfilling with silicone medical adhesive.
9. The central element can be designed to sustain high tensile loads, for those applications that require it. For instance the central element can be a larger (i.e. 7×7) solid MP35N cable, surrounded by smaller Ag-core MP35N cables, coibles, or open lumens. Alternatively, the central element can be a thicker-walled HSTF or ePTFE tube (i.e. with tensile properties similar to “Glide” dental floss), or a tube to house a fiber such as ePTFE (ala “Glide” dental floss), polyester, LCP, UHMWPE etc. or extruded element such as PEEK, PEKK, or polysulfone or other suitable material, which is capable of sustaining the required loads (
10. The final lead body assembly can be housed in a silicone or polyurethane overlay tube. Besides using this approach to provide a protective jacket with other materials of proven biocompatibility and biostability, an overlay can be used make the lead body isodiametric, for instance to butt-up with the ends of the defibrillation electrodes.
11. Any of the conductors used in these configurations can have additional redundant insulations composed of chemically different materials. For instance polyimide coated wire, or anodized tantalum wire, can be used to produce coils/cables.
12. Color additives or use of different combinations of HSTF and ePTFE layers, to produce differences in appearance or contrast can be used to facilitate differentiation of circuits, either visually or via pattern recognition techniques.
13. In addition to using HSTF and ePTFE as tape materials (which are chemically composed of PTFE), ETFE or other suitable materials which can be produced in tape form and which has acceptable mechanical, electrical, biocompatibility, and biostability properties can be used. One advantage with using ETFE or other materials instead of HSTF/ePTFE, is to provide a structure which can be exposed to e-beam or any other irradiation process used for sterilization, without significantly degrading mechanical/electrical properties, i.e. PTFE is not as resistant to radiation as other materials.
14. Cables served with same orientation as outer filaments of cables are less prone to bird-caging (e.g. 1×19 cables with a right-hand lay of the outer 12 filaments should be served in a right-hand orientation around the central coil liner to prevent bird-caging or opening-up of the filaments) (
15. Use of an ePTFE material for the inner layer of a coil liner, which is less “spongy” and less prone to shedding or “hairing” results in improved coil stringing, stylet passage, and helix extension requirements, e.g. material must be less prone to “piling up” or shedding of material with coil movement.
16.
NG2 Tachy is a sub-5 French, extendible/retractable, stylet delivered, IS-4 connector lead body platform. The lead body 2501 (
The NG2T Quadripolar lead is a lead that utilizes a modified fluoropolymer (mPTFE) for the primary insulation. The major benefits of using the mPTFE material include: thin layers of insulation which are mechanically robust, have high dielectric strength, and improved resistance to creep over traditional ETFE and PTFE. The use of these materials has also led to advances in manufacturing processing and a benefit to lead building. The mPTFE subassembly utilizes an outer ePTFE wrap to bundle the insulated cables and coil liner together. Windows and end cuts are made utilizing automated laser technology to prepare the subassembly for further manufacturing processing. A unique buried fitting approach (US Patent 2005/0240252 incorporated by reference in its entirety) provides the foundation for laser welding the defib coils to the subassembly. The method of assembly of the mPTFE insulation layers allows the fittings to first be crimped on the cables before insulation is layered over the cables and fittings. Upon completion of the subassembly, the fittings are then exposed with a small laser ablated window and minimize any unnecessary openings to expose the lead body. Furthermore, the skill, tools, time, and energy is no longer needed to string conductors through the multilumen, nor open the multilumen at multiple places to manipulate the conductors and cross-grooves.
The mPTFE material and subassembly provides the thin insulations necessary to produce a sub-five french lead, while still providing tough, creep resistant materials at very high dielectric strengths. An additional benefit of the mPTFE subassembly with the NG2T Quadripolar lead is the ability to utilize the Sprint Fidelis conductor coil for extension/retraction and the acceptance of a 0.014″ stylet.
The mPTFE subassembly is unique in its multi-axial design (
The mPTFE has been mechanically modified to resist abrasion and creep and provide high dielectic strength at very thin layers. The mPTFE is assembled with a wrap process that provides tight tolerances of layers and pin-hole free insulative layers. The inner conductor coil liner is a composite of mPTFE and expanded PTFE (ePTFE) to provide electrical isolation as well as resistance to kinking and the lead handling characteristics. The cable conductors and coil liner are bundled together with an outer ePTFE layer. The outer, tissue contacting layer, is a protective non-insulative tubing used to aide in lead handling and provide isodiametric geometry for ease of venous entry and lead extraction. The overlay tubing may be made of SME polyurethane or PurSil co-polymer. The proximal connector will use an IS4 configuration to connect to a device. The lead accepts a 0.014″ (blue, grey) or smaller stylet.
A 7 french introducer and a 6.6 french lead body. Below is a table comparing MDT market released leads RV electrode designs for dimensions, surface and shadow areas to that of NG2 tachy.
Silicone rubber backfill prevents in-growth of fibrotic tissue into and under the defibrillation electrode coil filars. Approximately 50%, 180° of the interior diameter, of wire surface to be covered with silicone adhesive. The remainder is wiped away during the manufacturing process leaving the outer surface, 180°, free of silicone rubber. See
The quality of the embedment process can vary and may be difficult to evaluate visually. The larger wire size of previous ICD leads improves the manufacturability of the backfill process; larger surfaces are easier to clean. The smaller wire size of the NG2 Tachy creates smaller crevices that can retain silicone rubber. The figure above show the differences between a 180 backfill to an 80 exposed surface. The resultant area is reduced by over 60%.
It was concluded that the TXD lead design is capable of having adequate surface area for comparable defibrillation performance to previously release ICD leads.
In addition a flat wire approach (which eliminates the need to try to clean the crevices) and alternative embedment processes may be used.
A separate backfilled subassembly allows the defib coil to be embedded with a uniform substrate before stringing onto the lead body, which has a non-uniform diameter (cables wrapped around the coil liner are non-uniform) and also will allow the composite stiffness in the defibrillation coil region to be reduced (see Stiffness section).
Pre-backfilled coils examples are shown in
Examples of 5 weld joint design concepts that have been explored for connecting the defib coil to buried crimp sleeve joint are shown in
Welding the filars together to form a ring or attaching a ring to the defib coil (
Leads have been made that meet a 3.6 psi tip stiffness requirement. The lead body subassembly (LBS) was made with a cable pitch of 0.812″ and an ePTFE (T5) outer wrap material that was treated with FEP to adhere it to the cables and the coil liner. The SVC cable was then able to be peeled out of the LBS without losing the pitch or having to remove the outer wrap. The SVC cable was cut 0.5″ distal of where the SVC coil would be placed.
These leads had a defib coil that was backfilled as a separate subassembly using FEP tubing (0.049″ OD) as a mandrel. The FEP tubing was stretched and removed so that the defib coil assembly could then be strung onto the lead body. The subassembly was then bonded to the lead body only on the ends. Two different defibrillation coils were used, a 0.005″ round wire coil and a 0.003″×0.007″ flat wire coil. Both leads showed acceptable tip stiffness, per plan RATR1572. The summary chart is shown in
Constriction of the LBS can effect stylet passage and the number of turns to ext/ret the helix. Constriction of the coil liner is caused by the non-uniformity of wrapping the cables around the coil liner.
A 0.026″ tooling stylet is being used to assess constriction at the LBS level. 100% testing should be done during development. Current requirement is free passage (insertion and withdrawal) of tooling stylet. Implementation of low torsion modifications to the cable serving equipment and were successfully able to make stylets pass freely and also make them stick.
The lead body subassembly design incorporates a buried crimp sleeve used to make a weld connection from the defibrillation coil to the cable. To expose the sleeve for this connection a laser is used to ablate the over wrap and the mPTFE cable insulation layers. An example of the buried sleeve in the LBS assembly is shown in
The current crimp sleeve design is part number A08157-001. This crimp does not close well or uniformly, see
The approach is to re-dimension the crimp sleeve to allow for more uniform shape and reduced seam gap. Two different sizes of round titanium tubing have been ordered and will be evaluated with current tooling. The new sleeves will be 0.003″ thick and 0.050″ long because this is worse case from a welding and processing stand point.
The current concept has three sleeve head components. These are required for assembly purposes since the cables are part of the LBS and the ring electrode needs to be sandwiched. This results in multiple joints that need to be bonded and reduces the area in the sleevehead for coil liner bonding and places overlapping joints in areas that may be needed for MRI feature as project progress. An alternative two-piece design and an insert molded and/or two-part electrode is currently being designed for the next concept. This concept eliminates two joints that were previously located behind the seal and eliminates possibility of fluid leakage through bonded areas and incorporates steroid MCRD. Additional information on the prior sleeve design/assembly method and the proposed new design are shown in
Potential advantages/features of the two part design concept;
Proximal Sleeve allows for the coil liner to extend past the electrode ring. Increased coil liner bond length and redundant insulation past the electrode ring.
Proximal sleeve has insert molded ring option and allows the cable to be directly welded to a groove on outside of the ring. This eliminates the crimping and weld operations utilized in current 3 part design.
Proximal sleevehead design incorporates a feature to aids postioning the defib coil and the transition from the lead body/defib coil to the sleevehead.
Integrated design eliminates joints in sleevehead
This two part design requires that the electrode ring be either insert molded into the proximal sleevehead (
Insert molding reduces handling of the TiN coating on the electrode ring and does not require an additional welding operation to close a hinge as in
Space used for clearances between the ring and the sleevehead are not needed and can be incorporated into the wall thickness of the proximal sleevehead and the ring.
Minimizes damage to ring caused by additional welding and fixturing operations which are required for hinged and two part concepts.
Eliminates alignment and position requirements during lead assembly.
The NG2T helix is smaller than the current HV leads.
The helix is planned to be supplied as a welded subassembly. This lead incorporates two novel C-Stops (
The distal sleeve will incorporate an MCRD that is bonded to the outer diameter of the sleevehead. The MCRD is based on the 4196 Lead MCRD (molded component with same silicone, steroid, and ratio).
Two MCRD variations are being investigated at this time (straight cylinder and a flare). One incorporates a flare at the distal end
The design/placement of the MCRD directly at the tip should provide several advantages:
1) Continues the practice of placing the MCRD/Steriod directly at the implant site.
2) Provide a thicker “soft” tip to minimize injury
3) Allow for tip to be enlarged but still be introducer compatible.
4) It is also been observed that this soft MCRD design will flare open and become larger when pressed against an object. This may help to reduce the potential for tip penetration.
5) Wrap around design allows increased steroid volume (˜3×4196) and still allow the indicator ring to be positioned close to the tip.
The concept is to use existing IS-4 connector module (P/N M924431A-002) and design and process for Model 6949M as much as possible.
Use of IS-4 connector module from MECC, P/N M924431A-002
Use of 1×19 cables and crimp blocks (all design and process work related to the joints between the cables and the connector module apply)
Use of 6949M conductor coil (all design and process work related to the joint between the coil and pin applies)
To compensate for the smaller lead body and to add additional strain relief, the NG2T adds a silicone
tubing bonded to
the overlay to make the transition to the IS-4 distal connector sleeve.
Evaluation testing was done for a Technology Phase review presented in January 2006. This design configuration (
A new thermal mechanical junction approach has been proposed. In the current process, a band or ring is strung onto the coil liner followed by a length of FEP tubing. Silicone tubing is dilated with heptane and slid over the top of the FEP and the band. The assembly is placed in the cavity of a thermal forming die and exposed to temperature for a set time duration. The silicone tubing is removed and the coil liner and FEP are cut to length. Alternate processing schemes in which the FEP is processed first (at higher temperature) and then a band or ring made of urethane or some alternative with a slot or hinge is assembled onto the coil liner and thermally processed at lower temperature are also options.
This joint will be loaded in tension and will need to meet a tensile design target
This joint also will be tested in torsion
Plasma treatment of the coil liner/cable(s) will be necessary
Use of thermal/mechanical approach with a ring (metallic or other) and FEP tubing is needed to pass testing
Bond length and diameter necessary for strength can be designed into sleevehead to allow the distal end to fit through a 5 Fr introducer
Tooling capability to control and minimize FEP diameter to fit into sleevehead
Fixturing is needed to provide thermal isolation of cable and coil liner
Tip to ring spacing and tip to RV spacing (13 mm) is adequate.
A piece part component made from FEP or PFA can be thermo-bonded onto another fluoropolymer such as PTFE or ETFE to create a useful junction on implantable medical leads. This thermo-mechanical joining process results in a strong adhesive-like bond between the polymers. The junction formed can be used as a tensile or torsional bearing member or as a feature for assembly to other components. Due to the difficulty of obtaining good adhesion to fluoropolymers such as PTFE, this process allows leads to achieve strong mechanical joints without adhesives. Welding methods like ultrasonic welding or laser may also allow joining of these flouropolymers types in place of thermo processing with traditional heating methods such as thermal die bonding or hot air fixtures.
The use of FEP as a thermal bonded component on our PTFE insulation achieves a very strong bond not obtainable with other types of adhesive bonds. The thermal bonded FEP component allows us to locate other lead components adjacent to the FEP and results in a joint that can have high composite tensile strength or potentially be used to transfer torque loads. The challenges posed by the chemical resistant and bond resistant nature of PTFE can be overcome with this FEP thermal bond technique.
Multiple distal joint designs using an FEP thermal bonded component on our PTFE liner have been developed that will allow our NG2 Tachy lead to have a strong distal end connection. High distal composite joint strengths will allow chronic lead extraction from patients with less risk of lead separation/breakage and facilitate easier lead removal by the physician. Use of an FEP thermal bond joint is also being studied for Proximal tubing connection on the IS-4 connector. The use of an FEP component thermal bonded to PTFE insulation will likely be used on most future lead designs by Medtronic as a means of achieving strong bond joints in multiple locations that require significant tensile properties. Determine effect of FEP Thermo bond and Polyurethane ring lengths on resulting composite pull forces and suitability of these materials for use as the mPTFE coil liner distal end connection. The goal is to achieve 4.5 lbs. average pull force of the distal end connection.
Through this study it will be determined if the Polyurethane 75D tubing can provide sufficient strength as a rigid member for bonding to the proximal sleevehead while using it in conjunction with thermal bonded FEP segment for NG2 distal design concept.
Two lengths of FEP thermo-bond tubing (0.060/0.090″) were built with two urethane ring lengths (0.060/0.090″) to determine the affect of component length on composite pull strength as potential NG2 distal joint design.
3 Groups of N=30 Samples were assembled using following described method: An FEP tubing segment is thermo-bonded to PTFE coil liner at 800° F. for 16 seconds. A block or tubing is located against proximal side of FEP Tube to hold maintain a square edge on FEP tube during thermo cycle. A silicone tubing over the FEP during thermal bond contains molten FEP and ensures adequate heating of PTFE liner. After thermo processing, silicone tubing is removed and a polyurethane ring is located proximally against FEP segment. An extruded 75D tubing (0.047 I.D/0.005 wall) is bonded onto FEP and urethane ring with tab 006 urethane adhesive to simulate distal sleevehead. Completed subassembly is shown in
Photo Image of all 4 FEP/Polyurethane Ring sample length combinations are attached as
Two lengths of FEP thermo-bond (0.060/0.090″) were pull tested with two urethane ring lengths (0.060/0.090″) to understand affect of component length on composite pull strength as potential NG2 distal joint design.
The graphite cylinder tooling used to form edge of FEP during thermal bond resulted in best edge shape as determined by pull test data. The absence of a conductor coil inside the PTFE liner during pull test, may have reduced pull strength by allowing the FEP to pull through urethane ring due to lack of support to PTFE liner while elongating during pull test.
The aluminum block tooling for forming FEP removed excessive heat from PTFE liner during thermo-bond, and caused high occurrence of FEP delamination at a low force pull force. These samples performed worse than other two Sample sets.
The FEP was later pull tested off of PTFE liner at forces of 3.81 to 4.72 lbs between the different component lengths studied, indicating that heat loss during thermal bond was minimal using the silicone tube as tooling method.
Using the polyurethane ring at the 0.060 or 0.090″ length does not have adequate mechanical strength to achieve 4.5 lb. pull force goal due to its inability to prevent FEP from pulling through urethane ring at forces over 3 lbs.
This application is a continuation-in-part of U.S. patent application Ser. No. 10/830,597, filed Apr. 23, 2004, entitled NOVEL MEDICAL DEVICE CONDUCTOR JUNCTIONS.
| Number | Date | Country | |
|---|---|---|---|
| Parent | 11549284 | Oct 2006 | US |
| Child | 12324018 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 10830597 | Apr 2004 | US |
| Child | 11549284 | US |
